Method and apparatus for the non-invasive sensing of glucose in a human subject

ABSTRACT

An apparatus for a non-invasive sensing of biological analytes in a sample includes an optics system having at least one radiation source and at least one radiation detector; a measurement system operatively coupled to the optics system; a control/processing system operatively coupled to the measurement system and having an embedded software system; a user interface/peripheral system operatively coupled to the control/processing system for providing user interaction with the control/processing system; and a power supply system operatively coupled to the measurement system, the control/processing system and the user interface system for providing power to each of the systems. The embedded software system of the control/processing system processes signals obtained from the measurement system to determine a concentration of the biological analytes in the sample.

CROSS REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of U.S. patent application Ser. No.11/451,864, filed Jun. 13, 2006, and Provisional Patent Application No.60/690,418, filed Jun. 14, 2005, both entitled “Method and Apparatus forthe Non-Invasive Sensing of Glucose in a Human Subject”, which arehereby incorporated by reference in their entirety.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates, in general, to noninvasive sensing ofbiological analytes in the capillary vessels and in interstitial fluid.More specifically, the present invention relates to a method and anapparatus for the determination of blood glucose, lipids and/or alcoholconcentration at regular short intervals on a continuous basis or ondemand.

2. Description of Related Art

Diabetes is a group of diseases characterized by high levels of bloodglucose resulting from defects in insulin production, insulin action, orboth. The Diabetes Control and Complications Trial (DCCT), a ten yearclinical study conducted between 1983 and 1993 by the National Instituteof Diabetes and Digestive and Kidney Diseases, demonstrated a directpositive correlation between high average blood glucose levels, known ashyperglycemia and the development of devastating complications of thedisease that affect the kidneys, eyes, nervous system, blood vessels andcirculatory system. Treatment includes insulin injections, oralmedication, diet control and exercise. Adjustment of the user's regimenby a physician to control hyperglycemia requires routine self-monitoringof glucose levels three or more times per day. Currently persons withdiabetes measure their glucose levels by using invasive blood glucoseinstruments that measure glucose using expensive disposable test stripswhere a small sample of blood obtained from a finger or the forearm isapplied. The procedure is very painful and often results in chronicnerve ending damage. This is one reason many diabetes patients foregomonitoring risking the development of serious complications.

Many prior art systems utilize diffuse reflectance spectroscopy todetermine blood glucose concentration in tissue. For instance, U.S. Pat.No. 6,097,975 to Petrovsky et al. discloses an apparatus and method fornon-invasively measuring blood glucose concentration. The apparatusprojects a beam of light (2050-2500 nm) to a selected area of the bodythat is rich in blood vessels, such as the inner wrist or ear lobes. Theprojected pulse of light is transmitted through the skin, tissues andblood vessels, partially absorbed by glucose in the blood and partiallyscattered, diffused and reflected off of irradiated structures backthrough the blood vessels, tissue and skin. The luminous energy of thereflected light is then collected by a receiving detector, converted toan electrical signal proportional to the glucose concentration in theblood of the subject and analyzed. The wavelength range of the preferredembodiment disclosed in this reference utilizes the wavelength range of2050-2500 nm.

U.S. Pat. No. 6,016,435 to Maruo et al. discloses a device fornon-invasive determination of a glucose concentration in the blood of asubject. The device includes a light source, a diffraction grating unitas a spectroscope of the light provided by the light source and astepping motor unit for controlling a rotation angle of the diffractiongrating to provide near-infrared radiation having successive wavelengthsfrom 1300-2500 nm. The device further includes an optical fiber bundlehaving a plurality of optical fibers for projecting the near-infraredradiation onto the skin of a subject and a plurality of second opticalfibers for receiving the resulting radiation emitted from the skin. Alight receiving unit is connected to the second optical fibers and aspectrum analyzing unit determines the glucose concentration in theblood through the use of spectrum analysis based on information from thelight receiving unit. This invention differs from the present inventionin that it utilizes a continuous spectrum lamp and a diffraction gratingwith mechanically moving parts.

U.S. Pat. No. 5,533,509 to Koashi et al. discloses an apparatus fornon-invasive measurement of blood sugar level. The apparatus includes awavelength-variable semiconductor laser that tunes in small rangesaround wavelengths of interest producing a beam that is separated intotwo optical paths with a beam splitter and an integrating sphere thatcollects laser light transmitted or reflected after passing along anoptical path and made incident on an examined portion of skin in whichthe blood glucose level is determined by examining the derivative of theabsorbance spectrum. The present invention differs from this referencein that the skin is probed over the entire range with a plurality ofwavelengths and not just certain wavelengths, and the absorbancespectrum, not the derivative of the absorption spectrum, is used todetermine glucose concentration.

United States Patent Application Publication No. 2005/0250997 to Takedaet al. discloses an apparatus for determining a concentration of a lightabsorbing substance in blood. The apparatus includes a plurality ofphoto emitters that emit light beams having different wavelengths towarda living tissue. A photo receiver is adapted to receive the light beamswhich have been transmitted through or reflected from the living tissue.However, the preferred embodiment of this invention calls for only twolight emitting diodes; one at 680 nm and one at 940 nm.

United States Patent Application Publication No. 2005/0256384 to Walkeret al. discloses a non-invasive glucose sensor including at least onelaser (Vertical Cavity Surface Emitting Laser (VCSEL) or edge emitting)and at least one photo detector configured to detect emissions from theemitter. The glucose sensor further includes a controller driving one ormore emitters by shifting emitter wavelength by 1-2 nm from a group ofselected wavelengths having center wavelengths of 1060 nm, 980 nm, 850nm, 825 nm, 800 nm, 780 nm and 765 nm. This enables measurement ofabsorption at a plurality of wavelengths and derivation of a glucoseconcentration measurement from the absorption measurement values. Thewavelength range of operation of this apparatus is outside thewavelength range of the present invention.

U.S. Pat. No. 5,703,364 to Rosenthal discloses a method for performingnear-infrared (NIR) quantitative analysis. The method includes the stepsof providing NIR radiation at a plurality of different wavelengths(600-1100 nm) for illumination of an object to be analyzed and varyingthe amount of time that radiation at each wavelength illuminates thesubject according to the output level of radiation at each wavelength soas to provide substantially similar detection data resolution for eachof the plurality of wavelengths. The wavelength range of operation ofthis apparatus is outside the wavelength range of the present invention.

U.S. Pat. No. 6,816,241 to Grubisic discloses a solid-statespectrophotometer for non-invasive blood analyte detection that employsa plurality of Light Emitting Diodes (LED(s)) that emit at distinct, butoverlapping, wavelengths in order to generate a continuous broadradiation spectrum and a linear detector array. It therefore differsfrom the present invention in that it uses an array of LEDs and an arrayof detectors.

Accordingly, a need exists for a system for the non-invasive sensing ofglucose in a human subject that utilizes a pulsable and selectablewavelength, a selectable intensity monochromatic laser radiation source,involves a spectroscopic referencing scheme that does not requiremechanical moving parts, and provides an improved instrument baselinestability by utilizing a dual-beam-double-reference spectrophotometer.

SUMMARY OF THE INVENTION

The present invention is directed to an apparatus for a non-invasivesensing of biological analytes in a sample. The apparatus includes anoptics system having at least one radiation source and at least oneradiation detector; a measurement system operatively coupled to theoptics system; a control/processing system operatively coupled to themeasurement system and an embedded software system; a userinterface/peripheral system operatively coupled to thecontrol/processing system for providing user interaction with thecontrol/processing system; and a power supply system operatively coupledto the measurement system, the control/processing system, the userinterface/peripheral system or any combination thereof for providingpower to each of the systems. The embedded software system of thecontrol/processing system processes signals obtained from themeasurement system to determine a concentration of the biologicalanalytes in the sample.

An absorbance spectrum obtained from the optics system may be used,together with a previously stored calibration vector, by thecontrol/processing system to determine the concentration of thebiological analytes in the sample. The sample may be one of interstitialfluid (ISF) of living tissue, the capillary bed of living tissue and/ora blood sample. The radiation source may be one of a selectable emissionwavelength and selectable emission intensity, Transversely Pumped,Counter Propagating, Optical Parametric Oscillator (TPCOPO) device or aselectable emission wavelength and selectable emission intensity laserdiode array. The radiation detector may be fabricated of InGaAs or Ge.

The biological analyte may be glucose, lipids or alcohol. An emissionspectrum of the radiation source may cover a range of about 1,200 nm toabout 1,900 nm and a responsivity of the radiation detector may cover arange of about 1,200 nm to about 1,900 nm, if the biological analyte isglucose or lipids. An emission spectrum of the radiation source maycover a range of about 800 nm to about 1,300 nm and a responsivity ofthe radiation detector may cover a range of about 800 nm to about 1,300nm, if the biological analyte is alcohol.

The user interface/peripheral system may be configured to alert a user,in case of pending hypoglycemia or hyperglycemia, by an audible toneand/or the display of a text message; alert other individuals equippedwith a Bluetooth alarm, in case of pending hypoglycemia, using aBluetooth module; determine the user's location using a GlobalPositioning System module and, in case of hypoglycemia, transmit anemergency text message to a telephone number or relay biological analyteconcentration data to a centralized server; and relay coded glucoseconcentration readings when they are taken to an insulin pump programmedto recognize the code and be in connection with the user, via theBluetooth module for the purpose of automatic release of insulin.

The at least one radiation source may be fabricated from opticalcrystals, semiconductor material monolayer structures or any combinationthereof. A semiconductor pump source may be integrated with a beamsteering structure and a TPCOPO layer to achieve emission wavelengthselection and intensity. In one embodiment, the at least one radiationsource includes a pair of GaAs Bragg reflectors with a GaAs TPCOPOactive layer, a GaAs narrowband coherent source pump and GaAsElectro-Optical beam deflecting layer. The pump source and beam steeringstructure may be parallel to the TPCOPO layer along the entire length ofa Bragg cavity or reside at one end of the Bragg cavity to allow forbeam steering before launching the pump source into the Bragg cavitycontaining the TPCOPO layer. Separate electrical connection means may bemade to the pump layer and the GaAs Electro-Optical beam deflectinglayer. An applied electric current to the pump layer may determine anintensity of emitted radiation, and an applied voltage to the GaAsElectro-Optical beam deflecting layer may determine a wavelength ofemitted radiation.

The present invention is also directed to a method for the non-invasivesensing of biological analytes in a sample through spectrophotometricreferencing utilizing two beams, each close in space (hereinafterreferred to as “TECS”) applicable to measuring interstitial fluiddiffuse reflectance. The method includes the steps of: providing anoptics system utilizing a first radiation source and a second radiationsource and a first radiation detector and a second radiation detector,thereby establishing four optical beam paths close in space through thesystem; modulating the sources with different time functions;configuring the optics system in a manner in which all optical elementsof the optics system transmit and/or reflect the beams; separating afirst pair of the beams and a second pair of the beams at one point inthe system, focusing the first pair of beams on a user's skin andfocusing the second pair of beams into a reference sample; demodulatingsignals produced by the first detector and the second detector andseparating signals due to the beams; and computing a spectrophotometrictransmittance as a ratio of a first ratio to a second ratio.

The first ratio may be the ratio of a skin diffuse reflectance signalincident on the second radiation detector due to radiation from thefirst radiation source to a reference diffuse reflectance signalincident on the second radiation detector due to radiation of the secondradiation source, and the second ratio may be an instrument signalincident on the first radiation detector due to radiation of the firstradiation source to an instrument signal incident on the first radiationdetector due to radiation of the second radiation source. Thespectrophotometric transmittance may be used to determine aconcentration of biological analytes in the sample. The optics systemmay have an area of separation between a sample beam and a referencebeam that is restricted to an interior portion of an optical glasselement. The area of separation between the sample beam and thereference beam may be protected by an enclosure.

These and other features and characteristics of the present invention,as well as the methods of operation and functions of the relatedelements of structures, will become more apparent upon consideration ofthe following description and the appended claims with reference to theaccompanying drawings, all of which form a part of this specification,wherein like reference numerals designate corresponding parts in thevarious figures. As used in the specification and the claims, thesingular form of “a”, “an”, and “the” include plural referents unlessthe context clearly dictates otherwise.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic view of an apparatus for the sensing of biologicalanalytes in a sample in accordance with the present invention;

FIG. 2 is a schematic view of the optics system of the apparatus of FIG.1;

FIG. 3 is a schematic diagram of an additional embodiment of the opticssystem of the apparatus of FIG. 1;

FIG. 4 is a detailed schematic view of the apparatus of FIG. 1;

FIG. 5 is a schematic diagram of a radiation source module in accordancewith the present invention;

FIG. 6 is a schematic diagram of a radiation detection module inaccordance with the present invention;

FIGS. 7 a-7 c are graphs illustrating one period of a discrete-timecapillary diffuse reflectance signal at the output of the detector, anexploded view thereof and at the output of a switched integrator,respectively; and

FIGS. 8 a-8 c are block diagrams of a transversely pumped counterpropagating optical parametric oscillator in accordance with the presentinvention.

DETAILED DESCRIPTION OF THE PRESENT INVENTION

For purposes of the description hereinafter, the terms “upper”, “lower”,“right”, “left”, “vertical”, “horizontal”, “top”, “bottom”, “lateral”,“longitudinal” and derivatives thereof shall relate to the invention asit is oriented in the drawing figures. However, it is to be understoodthat the invention may assume various alternative variations, exceptwhere expressly specified to the contrary. It is also to be understoodthat the specific devices illustrated in the attached drawings, anddescribed in the following specification, are simply exemplaryembodiments of the invention. Hence, specific dimensions and otherphysical characteristics related to the embodiments disclosed herein arenot to be considered as limiting.

With reference to FIG. 1, an apparatus 1 for the determination ofbiological analytes includes an Optics System 11, a Measurement System12, a Controller/Processor System 13, a User Interface/Peripheral System14, a Power Supply System 15, and an embedded software system (notshown). Each system contains several sub-systems.

With reference to FIG. 2 and with continuing reference to FIG. 1, OpticSystem 11 includes a radiation source module 17, a radiation detectionmodule 23 and a fiber optics probe 44 operatively coupled to the sourcemodule 17, the detector module 23 and skin 63 of a user via contactthrough a special attachment 47. Fiber optics probe 44 includes severalfibers 45 bundled together to transfer radiation from the source module17 to skin 63 and several other fibers 46 are bundled together to pickup the diffuse reflectance from skin 63 and transfer it to the detectormodule 23. Source module 17 may be, but is not limited to, one or moreTPCOPOs or a laser diode array. The source emission spectrum covers thewavelength range of 1,200 nm to 1,900 nm for glucose and lipidsdetection and 800 nm to 1,300 nm for alcohol detection, emitting at 64to 256 distinct wavelengths. The detector is responsive equivalentlyover the same range. Detector module 23 may be, but is not limited to, aGe detector, an InGaAs detector, or an extended InGaAs detector.

As discussed above, in one preferred and non-limiting embodiment, thesource module 17 is a laser diode array, e.g., an edge-emitting orsurface-emitting semiconductor laser diode array, an alternate laserdiode array, etc. In one embodiment, the laser diode array includesmultiple individual or discrete laser diode elements, e.g., 32-256individual elements, and each element has a unique center emissionwavelength with center wavelengths spaced evenly between the desiredendpoints of the range. For example, the wavelengths may be spacedevenly, such as at 5 nm intervals, between about 1200 nm and about 1900mm. Still further, each element is individually addressable with afiring or activation sequence, which is not necessarily successive overthe elements.

In one embodiment of such a laser diode array arrangement, the focalpoint of each element will be less than 200 μm in diameter. Theindividual line width of each element is a maximum of 2.5 nm (atfull-width-half-maximum). The power output of the element is betweenabout 25 mW and 300 mW, and the element duty cycle is 0.4% to 4%. Theelement rise time is a maximum of 5 nanoseconds, with an element “on”time of 1 μsecond to 100 μsecond. The optical power variability of theelements exhibit a 5% maximum repeatability, and the optical powervariability between elements is a maximum of 50%. In operation, thelaser diode array radiation source 17 warm-up time to reach stabilitymay be not more than 30 seconds. The storage temperature range of thelaser diode array radiation source 17 is from about −25° C. to 70° C.,with an operation temperature range of 0° C. to 50° C. Finally, in thisembodiment, the element forward current is a maximum of 2.5 A, theforward voltage is a maximum of 1.2 V and the threshold current is amaximum of 1.0 A.

With reference to FIG. 3 and with continuing reference to FIG. 1, analternate embodiment of the Optics System 11 includes at least tworadiation sources, Source “1” 49 and Source “2” 50 and at least tworadiation detectors, Detector “1” 51 and Detector “2” 52.

Source “1” 49 and Source “2” 50 may be, but are not limited to, one ormore TPCOPOs or a laser diode array. Desirably, Source “1” 49 and Source“2” 50 are pulsable and selectable wavelength and selectable intensitymonochromatic laser radiation sources. The use of a selectable emissionwavelength solid-state radiation source lends to using a singlephotodetector and no need for a spectrograph, and therefore has theadvantages of small size, battery operation, wearability, improvedstability and improved drift. In addition, use of a source that iscapable of being switched on/off very rapidly and of emitting at onewavelength at a time, allows higher radiation power, resulting inincreased diffuse reflectance signal and signal-to-noise ratio due toISF, but especially due to capillary blood that is detectable andtherefore enabling probing of the capillary blood glucose in addition toISF glucose. As discussed above, such a radiation source may be aTPCOPO, a laser diode array or others. The laser diode array providesradiation at several wavelengths covering the required broad spectrum.While the TPCOPO uses only one laser diode as a pump, the laser diodearray uses one laser diode for each wavelength. A broad spectralcoverage source finds applications beyond spectroscopy wherevermonochromatic light sources have applications such astelecommunications, displays, room lighting, etc. Compact, highefficiency, rapidly and widely tunable solid-state monochromatic lightsources are applicable in all of these fields; however, individually,existing technologies such as monochromators, optical parametricoscillators (OPO), light emitting diodes (LED), laser diodes tuned viathermal, piezo-electric or electro-optic action, and dye lasers havesome but not all of the above features.

Detector “1” 51 and Detector “2” 52 may be, but are not limited to, Gedetectors, InGaAs detectors, or extended InGaAs detectors. The tworadiation sources and the two radiation detectors have identicalspectral coverage over 1,200 nm to 1,900 nm for glucose and lipidsdetection and 800 nm to 1,300 nm for alcohol detection. The sources emitM (64-256) distinct wavelengths and the detectors are responsiveequivalently over the same range.

A first mirror 53 and a first lens 54 direct two beams 64 and 65 fromthe two sources onto a beam splitter 55 where a small portion of theradiation power is reflected and is directed through a second lens 56 toDetector “1” 51. Second lens 56 may be, but is not limited to, a Kohlerlens that images the aperture of beam splitter 55 onto Detector “1” 51.Most of the optical power, however, is transmitted through the beamsplitter 55, a third lens 57 and a second mirror 60 to an immersion lens61 that is in contact with the user's skin 63. The beam 64 of Source “2”50 is focused onto a reference standard 62, such as spectralon, which isimmersed and protected in immersion lens 61, while the beam 65 of Source“1” 49 is focused on the skin 63. Immersion lens 61 is dimensioned to asize large enough to allow significant separation of the skin beam andthe reference beam to occur only within the glass of immersion lens 61.Immersion lens 61 is constructed from, for example, Bk-7, fused silica,or sapphire. Both beams are collected by pick-up optics 58 and 59 andconcentrated onto Detector “2” 52.

Detector “2” 52 is used to detect both the skin and reference signalthat form the biological beam pair, whereas Detector “1” 51 is used todetect instrument stability beams such as an instrument beam pair.Defining signals resulting from the optical paths of the two beam pairsof incident radiation on the detectors as: S₁₁ instrument signalincident on Detector “1” 51 due to radiation of Source “1” 49, S₁₂instrument signal incident on Detector “1” 51 due to radiation of Source“2” 50, S₂₁ skin diffuse reflectance signal incident on Detector “2” 52due to radiation of Source “1” 49, and S₂₂ reference diffuse reflectancesignal incident on Detector “2” 52 due to radiation of Source “2” 50.The transmission spectrum is computed as a ratio of two ratios:T=(S ₂₁ /S ₂₂)/(S ₁₁ /S ₁₂)  (Equation 1)

At any given time, during measurement, only one source is activated. Ifthe two beam pairs are very close in space, they encounter identicaltransmissions, reflections, and disturbances and the effects ofoptical/electro-optical component drifts and disturbances are canceledout. Therefore, the expense of using two radiation sources providessampling of the reference standard diffuse reflectance without having tomove mirrors while, in addition, the use of two detectors providesinstrument stability. Accordingly, this spectroscopic referencingscheme, TECS, does not require mechanical moving parts and providesimproved instrument baseline stability by utilizing adual-beam-double-reference spectrophotometer. This scheme utilizes twosources and two detectors, as described above, that form two beam pairseach sampled close in space that experience the same disturbances.

With reference to FIG. 4, and continued reference to FIG. 1, a moredetailed schematic diagram of one preferred embodiment of the apparatus1 of the present invention is shown. The centralized control componentof the apparatus 1 is the Controller/Processor System 13.Controller/Processor System 13 boots from a resident FLASH memory(non-volatile) that holds the program and executes the program fromresident SRAM (Static Random Access Memory) and controls the MeasurementSystem 12. Controller/Processor System 13, in conjunction with UserInterface/Peripheral System 14, performs a variety of functionsincluding, but not limited to, temporarily saves all diffuse reflectanceand dark signals in SRAM, processes the signals to develop theabsorbance spectrum, and subsequently determines glucose concentration,saves the data in FLASH memory, drives a buzzer 31, displays the data ona small size (1.5″×1.0″) monochrome or color graphics LCD 30 via the LCDController 29, accepts input from the user via Function Push ButtonSwitches 32, uploads data to a computer via the USB Interface 33 and USBConnector 34 or the BlueTooth Module 28, provides short distance remotealerts via the BlueTooth module 28, and determines user location via theGPS module 27 and provides long distance alerts via the GSM/GPRS module26. Another push button switch, Power On/Off Push Button 36 serves forturning the apparatus 1 on. Pressing the same switch 36 will turn theapparatus off, but only after invocation by the Controller/ProcessorSystem 13 via the display 30 and subsequent confirmation by the user viathe Function Push Button Switches 32. Controller/Processor System 13also contains a Real Time Clock (RTC) (not shown) that keeps track oftime even when the apparatus 1 is powered off and provides stamps ofdate and time to each measurement.

Controller/Processor System 13, in conjunction with UserInterface/Peripheral System 14, is thereby provided with the ability toperform a variety of functions. For instance, Controller/ProcessorSystem 13 can display the last glucose reading and the time it was takenon LCD 30 as well as calculate and display the trend and rate. It cancalculate and display on LCD 30 various statistics, such as movingaverage (trend) and daily moving min-max deviation over a selected timeperiod and plot them versus time on LCD 30 when requested. It canprovide the option to the user for selecting the units of glucoseconcentration mg/dL or mmol/L and can store up to a yearlong set ofglucose readings in nonvolatile memory together with time stampsreflecting the time they were taken, display, or upload to a computerwhen requested via USB interface 33 or Bluetooth module 28 as selected.

In cases of pending hypoglycemia or hyperglycemia, it can alert the userby an audible tone created by buzzer 31 and display a text message onLCD 30. Further, in cases of pending hypoglycemia, apparatus 1 can alertother individuals equipped with a Bluetooth alarm and located at adistance of up to 10 meters away using built-in Bluetooth module 28.Apparatus 1 can also determine the user's location through the use ofGPS module 27 and, in case of hypoglycemia, can transmit an emergencytext message to a telephone, such as emergency services “911” and/or anyother preprogrammed telephone number, including a centralized sever bybuilt in General Packet Radio Service (GPRS) or Global System for MobileCommunication (GSM) or simply relay glucose concentration data tocentralized server for the purpose of telemedicine. Apparatus 1 may alsorelay glucose concentration readings at the time they are taken to aninsulin pump, connected to the user, via Bluetooth module 28 and,together with the insulin pump, form an artificial pancreas. Ifapparatus 1 is used in such a manner, Controller/Processor System 13must code the data by a pseudorandom sequence shared by both apparatus 1and the insulin pump in order to avoid interference with other users whohappen to be nearby.

With further reference to FIG. 4, Power Supply System 15 contains arechargeable small size battery 37. Battery 37 may be, but is notlimited to, a Li-Ion type battery. A Power Supervision/BatteryProtection subsystem 35 protects battery 37 from over-discharge andshort circuit conditions and notifies Controller/Processor System 13when the battery voltage is low and must be recharged. It also containsDC/DC Converter Voltage Regulator sub-systems 39, 40, 41, and 42 thatproduce the necessary voltages for biasing all circuits and voltagedistribution for various sub-systems with on/off capability under thecontrol of Controller/Processor System 13.

Apparatus 1 may determine its status by self-testing Power Supply System15 and Measurement System 12 prior to each measurement and warn the userin case of faults via buzzer 31 or LCD display 30. Apparatus 1 alsomonitors battery voltage and warns the user when replacement isnecessary between glucose readings without interruption in monitoring,as battery charging will take place outside the unit to perpetuatecontinuous monitoring. Apparatus 1 also determines battery status bymonitoring duration of service (how long the battery holds its charge innormal use) and warns the user when a new battery is necessary.Apparatus 1 may also automatically power down some circuitry betweenmeasurements in order to preserve battery life. Apparatus 1 also has theability to request and obtain confirmation via User Interface/PeripheralSystem 14 to turn off apparatus 1 in response to Power On/Off PushButton 36 activation in order to avoid accidental power off.

Measurement System 12 includes the Radiation Source Module 17, a SourceModule Temperature Controller 16, an EOBS Driver 20, a 16-bit WavelengthD/A Converter 21, a VCSEL Driver 18 and a 16-bit Intensity D/A Converter19. It also includes Radiation Detection Module 23, a Detector ModuleTemperature Controller 22, a Detector Amplifier 24, and a Signal A/DConverter 25.

With reference to FIG. 5 and with continuing reference to FIGS. 1 and 4,the circuit of Radiation Source Module 17, along with the circuits ofEOBS Driver 20 and VCSEL Driver 18 are shown. Source “1” 49 or Source“2” 50 (LD1-LDM) has a radiation intensity that is selectable up to 500mW by the voltage level of the Intensity D/A converter 19 via VCSELDriver 18 and is switchable on/off by switching transistors SLD1-SLDM 70for a short period (1-100 μs) under command by Controller/ProcessorSystem 13 over a Select control 68 and a Decoder 69. The source emissionwavelength is also selectable by the voltage level of Intensity D/Aconverter 21 via EOBS Driver 20 over the mentioned range and mentioneddistinct wavelengths. Radiation Source Module 17 also contains athermoelectric cooler 71 (TEC) and an associated thermistor 72 to enabletemperature control by Source Module Temperature Controller 16 at 25° C.

With reference to FIG. 6 and with continuing reference to FIGS. 1 and 4,the circuit of Radiation Detector Module 23, along with the circuit ofthe Detector Amplifier 24, is shown. Radiation Detector Module 23includes one or two detectors 51, 52 that convert the optical diffusereflectance signals to electrical signals and a TEC 76 and an associatedthermistor 77 to enable temperature control of the detectors by DetectorModule Temperature Controller 22 at 10° C. Detector Amplifier 24 processthe electrical diffuse reflectance signal by a switched integratorcircuit 74 and correlated double sampling circuit 75 under switchcontrol by Controller/Processor System 13 and in synchronicity withswitch control of the radiation. A 24-bit Signal A/D Converter 25digitizes the reflectance signal and outputs it to Controller/ProcessorSystem 13. The acquisition of one full set of data, including skin,reference, and dark signals over all wavelength channels, takes 1-20 ms.Within a measurement time of approximately 10 seconds acquisition isrepeated N times (500-10,000). The measurement, in continuous mode, canbe repeated every 5 minutes with battery replacements every 12 hours orevery 10 minutes with battery replacements every 24 hours.

The software of Controller/Processor System 13 processes the signals tominimize noise first, then computes transmittance and the absorbancespectra, and finally computes analyte concentrations. Theoretically,transmittance is defined as the ratio:T=I/I _(o) =e ^(−kd)(Beer-Lambert law)  (Equation 2)

I denotes the intensity of the diffuse reflectance in response toincident radiation of intensity I_(o), k denotes the extinctioncoefficient (tissue or reference standard), and d denotes thepenetration distance. In the case of ISF, the skin diffuse reflectance,the reference diffuse reflectance, and the photodetector dark currentare measured. In the following description, bold letters denote vectors.The transmittance spectrum is computed as a double ratio I_(skin)/I_(o)divided by I_(ref)/I_(o). Therefore, T=I_(skin)/I_(ref), hence bypassingthe need to measure incident radiation, I_(o). The detected radiation,R_(skin), R_(ref) includes a strong component D₂ due to detector darkcurrent, which must be subtracted, plus uncorrelated noise. Therefore,after mean centering all signals the transmittance spectrum is computedas T=(R_(skin)−D₂)/(R_(ref)−D₂) and the absorbance spectrum is bydefinition:X=−log T  (Equation 3)

The software sorts the sampled signals of skin, reference, and dark timesequences in a 3×N×M array. Each signal sequence skin, reference, anddark is low-pass filtered at 0.5 Hz by a sharp zero-phase digital filterto reduce excessive noise. To develop the ISF absorbance spectrum, thetransmittance spectra are calculated first for each set of acquireddata, then averaged, and absorbance is computed using the averagetransmittance spectrum. The development of the capillary absorbancespectrum, however, requires more processing. The skin diffusereflectance signal, at each wavelength channel, contains a large DCpart, due mostly to ISF diffuse reflectance with a small part due tocapillary diffuse reflectance (˜1%), a small part due to detector darksignal and a large portion due to uncorrelated white noise. This signalis modulated by heart pumping action with high excursions occurring atthe systolic phase of the heart and low excursions occurring at thediastolic phase. Accordingly, apparatus 1 provides for the measurementof glucose in the capillary vessels by utilizing a spectroscopicreferencing scheme that does not require a reference standard and/ormechanical moving parts. Apparatus 1 thereby offers improved instrumentbaseline stability and processing that involves optimized synchronousdetection of the time signal at each wavelength of the extremely smalland slowly varying heart pulse modulated diffuse reflectance signal andforming the transmittance as a ratio of the maxima to the minima. Thisreferencing scheme samples one path that changes minutely close in timeat the minimum and maximum photon path changes during each heart pulse.

With reference to FIGS. 7 a-7 c, a single cycle of this signal at onewavelength channel, at the output of the detector, is shown. The signalis discrete in time because of the switching of the radiation source onfor 1-100 μs and off for 1-20 ms between wavelength channels. Thefrequency spectrum of this signal contains one set of components at DCplus components at a heart rate as mentioned above and more sets ofthese signals at fundamental and harmonic frequencies of the switchingsignal. To apply Pulse Differential Spectroscopy (PDS), the excursionsmust be determined. Operating around DC this is accomplished as follows.Both signal sequences skin and dark are low-pass filtered at 2 Hz by asharp zero-phase digital filter to reduce excessive noise. They are thenhigh-pass filtered at 0.5 Hz by a sharp zero-phase digital filter toeliminate the strong DC component. The excursions can then be determinedvia FFT or by demodulation with a synchronous replica of the heart pulsesignal.

In general, in one embodiment, the method of spectrophotometricreferencing according to the present invention utilizes PulseDifferential Spectroscopy. In general, the use of Pulse DifferentialSpectroscopy in such an application provides an absorbance spectrum thatis formed by the ratio of a spectral measurement taken at the diastolicstate to a spectral measurement taken at the systolic state, and at eachemission wavelength of the radiation source, e.g., a laser diode array,etc. This means that the signal, as measured by the magnitude of thefrequency component at the systolic/diastolic heart rate of theFourier-transformed-time-sampled signal at each emission wavelength ofthe source 17, forms an absorbance spectrum.

Further, narrow band sources across the entire wavelength range ofinterest (e.g., 1,200 nm to 1,900 nm) are used, and the output power ofeach narrow band emitter is set to the maximum optical signalsustainable on the skin. These sources are set to acquire a full,high-power spectrum of the PR skin signal at least 100 times per second.The systolic/diastolic variations modulate the bulk skin optical PRsignal collected by the sensor or detector. The optical signal componentdue to the interstitial fluid is common to all phases of modulation ofthe optical signal caused by the heart pulse and is therefore negated orrejected. The measurement signal at the diastolic state contains bulkskin signal and the base capillary signal, whereas the measurementsignal at the systolic state includes the bulk skin signal, the basecapillary signal and the perturbed capillary signal. The resulting ratioleaves only the perturbed capillary signal, which is used to calculatethe level of the biological analyte, e.g., glucose.

A replica of the heart pulse signal can be developed by estimation ofpulse rate using the time sequence of the skin diffuse reflectancesignal at a channel with a wavelength around 1275 nm. Radiation at thiswavelength penetrates the epidermis and reaches the capillary bed muchdeeper than any other wavelength. The transmittance is computed asmentioned above by averaging the peak positive excursions to/fromR_(skin) and averaging the peak negative excursions to/from R_(ref)since there are 6-12 cycles over the measurement period. Alternatively,the excursions can be determined similarly by operating at thefundamental of the switching frequency. However, this method requires,in addition, down-conversion to DC by multiplication of the signals by asynchronous replica of the switching signal.

Finally the absorbance spectrum is used together with a previouslystored calibration vector b, to predict glucose concentration:y_(P)=Xb  (Equation 4)

The calibration vector is obtained by Partial List Squares as:b=(X ^(T) X)⁻¹ X ^(T) y _(R)  (Equation 5)

y_(R) are reference readings obtained with an accurate invasive device.The number of required acquired spectra and invasive reference readingsfor the purpose of calibration can be reduced drastically by adding apriori knowledge about the spectra in determining the calibration vectoras discussed in the article entitled “On Wiener filtering and thephysics behind statistical modeling” by Marbach. Accordingly, therequired individual calibration time may be reduced from many days to afew hours.

With reference to FIGS. 8 a-8 c, the TPCOPO provides the means ofobtaining optical parametric oscillation, and similar to a conventionalOPO, the TPCOPO requires a pump. Tuning is achieved by changing theangle of incidence of the pump beam. The TPCOPO can be fabricated fromconventional non-linear optical crystals such as, but not limited to,LiNbO3, KTP and others. However, the transverse design nature of theTPCOPO also allows for fabrication from semiconductor materials such asGaAs and ZnSe monolayer structures. By integrating a VCSEL semiconductorpump source and an electro-optic beam steering structure (EOBS) with aTPCOPO, all of the previously mentioned characteristics of a tunablelight source are achieved. For instance, the device may be comprised ofa pair of GaAs Bragg reflectors with the GaAs TPCOPO active layer, aGaAs solid state narrowband coherent source serving as a pump such as aVCSEL or others and a GaAs electro-optical beam-deflecting layer betweenthem.

The TPCOPO layer and Bragg reflectors are designed for the wavelength ofthe pump. In this embodiment, the pump and beam steering elements can beeither parallel to the TPCOPO layer along the entire length of the Braggcavity or they can reside at one end of the Bragg cavity to allow forample beam steering capacity before launching the pump into the Braggcavity containing the TPCOPO layer. Electrical connections for the meansof applying drive voltages are made to the pump and EOBS layersseparately. Electrical power to the pump determines the optical outputpower and the electrical voltage applied to the EOBS layer determinesthe optical output energy (i.e., frequency). The described structure canbe made either as a single element emitter or as an array. Thestructural layers of the TPCOPO shown in FIG. 8 are Bragg reflector 80,EOBS beam steering layer 81, pump 82, TPCOPO active layer 83, Devicesubstrate 84. In FIG. 8 a, the pump is located outside the Bragg cavity.This may be useful if the desired pump is not compatible with the EOBSor TPCOPO materials, the EOBS layer requires excessive path length foradequate beam steering or if the pump and or EOBS layers excessivelyabsorb the pump or TPCOPO output frequencies. In this configuration, theEOBS layer can be substituted with an acousto-optic or piezo-electricbeam steering layer and need not be “grown” onto the Bragg cavity. InFIG. 8 b, the pump and EOBS layers are placed inside the Bragg cavityfor higher conversion efficiency of the pump energy to output energy,but allow freedom of design for EOBS path length in the event the EOBSlayer requires multiple passes of the pump wave for adequate angulardeflection before entering the TPCOPO layer. In FIG. 8 c, the pump, EOBSand TPCOPO layers are stacked on top of each other. This is the simplestdesign assuming the EOBS layer effectively deflects the pump output andneither the pump nor the EOBS layer excessively absorb either the pumpor the output frequencies.

Although the invention has been described in detail for the purpose ofillustration based on what is currently considered to be the mostpractical and preferred embodiments, it is to be understood that suchdetail is solely for that purpose and that the invention is not limitedto the disclosed embodiments, but, on the contrary, is intended to covermodifications and equivalent arrangements that are within the spirit andscope of the appended claims. For example, it is to be understood thatthe present invention contemplates that, to the extent possible, one ormore features of any embodiment can be combined with one or morefeatures of any other embodiment.

The invention claimed is:
 1. An apparatus for a non-invasive sensing ofbiological analytes in a sample comprising: a) an optics systemcomprising at least one radiation source and at least one radiationdetector; b) a measurement system operatively coupled to the opticssystem; c) a control/processing system operatively coupled to themeasurement system, said control/processing system configured to executeembedded software; d) a user interface/peripheral system operativelycoupled to the control/processing system, said user interface/peripheralsystem configured for user interaction with the control/processingsystem; and e) a power supply system operatively coupled to themeasurement system, the control/processing system, the userinterface/peripheral system or any combination thereof for providingpower thereto, wherein the embedded software executed by thecontrol/processing system processes signals obtained from themeasurement system to determine a concentration of the biologicalanalytes in the sample, wherein the at least one radiation source isfabricated from optical crystals, semiconductor material monolayerstructures or any combination thereof, wherein a semiconductor pumpsource is integrated with a beam steering structure and a TPCOPO layerto achieve emission wavelength selection and intensity selection, andwherein the at least one radiation source is comprised of a pair of GaAsBragg reflectors with a GaAs TPCOPO active layer, a GaAs narrowbandcoherent source pump and GaAs Electro-Optical beam deflecting layertherebetween.
 2. The apparatus of claim 1, wherein an absorbancespectrum obtained from the optics system is used, together with apreviously stored calibration vector, by the embedded software system ofthe control/processing system to determine the concentration of thebiological analytes in the sample.
 3. The apparatus of claim 1, whereinthe sample is interstitial fluid of living tissue, the capillary bed ofliving tissue, a blood sample or any combination thereof.
 4. Theapparatus of claim 1, wherein the radiation detector is fabricated fromInGaAs, Ge or any combination thereof.
 5. The apparatus of claim 1,wherein the biological analyte comprises at least one of: glucose;lipids; and alcohol.
 6. The apparatus of claim 5, wherein an emissionspectrum of the radiation source covers a range of about 1,200 nm toabout 1,900 nm.
 7. The apparatus of claim 5, wherein a responsivity ofthe radiation detector covers a range of about 1,200 nm to about 1,900nm.
 8. The apparatus of claim 1, wherein the biological analyte isalcohol, and an emission spectrum of the radiation source covers a rangeof about 800 nm to about 1,300 nm.
 9. The apparatus of claim 8, whereinthe biological analyte is alcohol, and a responsivity of the radiationdetector covers a range of about 800 nm to about 1,300 nm.
 10. Theapparatus of claim 1, wherein the user interface/peripheral system isconfigured to: a) alert a user, in case of pending hypoglycemia orhyperglycemia, by an audible tone and/or display of a text message; b)alert other individuals equipped with an alarm, in case of pendinghypoglycemia, using an alarm module; c) determine the user's locationusing a Global Positioning System module and, in case of hypoglycemia,transmit an emergency text message to a telephone number or relaybiological analyte concentration data to a centralized server; d) relaycoded glucose concentration readings when they are taken to an insulinpump programmed to recognize the code and connected to the user, via thealarm module for the purpose of automatic release of insulin, or anycombination thereof.
 11. The apparatus of claim 1, wherein the pumpsource and beam steering structure are one of parallel to the TPCOPOlayer along the entire length of a Bragg cavity or reside at one end ofthe Bragg cavity to allow for beam steering before launching the pumpsource into the Bragg cavity containing the TPCOPO layer.
 12. Theapparatus of claim 1, further comprising: separate electricalconnections to the GaAs narrowband coherent source pump layer and theGaAs Electro-Optical beam deflecting layer.
 13. The apparatus of claim1, wherein said GaAs narrowband coherent source pump layer is configuredto use a received electric current to determine an intensity of emittedradiation.
 14. The apparatus of claim 1, wherein said GaAsElectro-Optical beam deflecting layer is configured to use an appliedvoltage to determine a wavelength of emitted radiation.